Intravascular ultrasound system for co-registered imaging

ABSTRACT

An intravascular ultrasound imaging system comprises a catheter having an elongated body having a distal end and an imaging core arranged to be inserted into the elongated body. The imaging core is arranged to transmit ultrasonic energy pulses and to receive reflected ultrasonic energy pulses. The system further includes an imaging engine coupled to the imaging core and arranged to provide the imaging core with energy pulses to cause the imaging core to transmit the ultrasonic energy pulses. The energy pulses are arranged in repeated sequences and the energy pulses of each sequence have varying characteristics. The reflected pulses may be processed to provide a composite image of images resulting from each different characteristic.

CROSS-REFERENCES

This application is a continuation application of U.S. application Ser.No. 12/902,460, filed Oct. 12, 2010, which claims the benefit of U.S.Provisional Application No. 61/256,543, filed Oct. 30, 2009 and U.S.Provisional Application No. 61/250,781, filed Oct. 12, 2009, thecontents of which is hereby incorporated by reference in theirentireties.

BACKGROUND

The present invention generally relates to intravascular ultrasound(IVUS) imaging. The present invention more specifically relates to IVUSsystems for co-registered imaging.

Intravascular ultrasound imaging is generally performed to guide andassess percutaneous coronary interventions, typically the placement of abare-metal or drug-eluting stent. Other applications of IVUS imagingcomprise further assessment of coronary artery disease.

Coronary stents generally have struts made of a metal, such as stainlesssteel or a cobalt chromium alloy. The metal stent struts provide asubstantially larger reflected ultrasound signal than blood and softtissue, such as neotissue grown over stent struts. The ability to detectand measure neotissue growth is particularly relevant for evaluating thestent healing process. Current commercially available IVUS systems havelimited ability to detect early neotissue growth, because of a limiteddetectable range of reflected ultrasound signals.

Atherosclerotic lesions that are prone to rupture, so called vulnerableplaques, are of increasing interest to interventional cardiologists. Onetype of vulnerable plaque thought to be responsible for a largepercentage of plaque ruptures is a thin-cap fibroatheroma wherein a thin(<65 .mu.m) fibrous cap overlies a mechanically unstable lipid-rich ornecrotic core. Current commercially available IVUS systems operate up toonly 40 MHz and have axial resolutions that are limited to approximately100 .mu.m. Consequently, current commercially available IVUS systemscannot reliably detect vulnerable plaques.

It is generally necessary to increase the imaging frequency in order toimprove spatial resolution. However, increased imaging frequency alsoleads to reduced contrast between blood and non-blood tissue that inturn makes difficult segmentation of the blood-filled lumen from theintimal plaque. Some automatic segmentation algorithms exploit thefrequency-dependent ultrasound properties of blood and non-blood tissuesas described for example in U.S. Pat. No. 5,876,343 by Teo. Real-time,automatic segmentation tools are often prone to errors which reducetheir utility in clinical practice.

Multi-frequency imaging has been developed for transthoracicechocardiographic applications. U.S. Pat. No. 6,139,501 by Roundhill etal. describes a system that simultaneously displays two B-mode images ofdifferent imaging frequencies and bandwidths. However, this techniqueuses both fundamental and harmonic imaging techniques and relies uponnon-linear propagation properties of tissue. Although harmonic imagingcan potentially provide better spatial resolution, harmonic imagingperformance in the near-field is limited. Further, harmonic IVUS imaginghas not been found to be practically useful.

Multi-frequency IVUS imaging can also be achieved by use of multipletransducer imaging catheters. However, multiple transducers addcomplexity and cost to the disposable imaging catheter and the imagingsystem. The potential need to co-register the images from the separatetransducers further complicates their practical use.

There exists a need for a technology that provides sufficient contrastresolution to guide percutaneous coronary interventions and sufficientcontrast and spatial resolution to detect stent healing and vulnerableplaques. Further, it is desirable that such a technology does notrequire any co-registration step between multiple images. Still further,it is desirable that such a technology does not substantially increasesystem and catheter complexity and cost over existing commercial systemsand catheters.

SUMMARY

The invention provides an intravascular ultrasound imaging systemcomprising a catheter having an elongated body having a distal end andan imaging core arranged to be inserted into the elongated body. Theimaging core is arranged to transmit ultrasonic energy pulses and toreceive reflected ultrasonic energy pulses. The system further comprisesan imaging engine coupled to the imaging core and arranged to providethe imaging core with energy pulses to cause the imaging core totransmit the ultrasonic energy pulses. The energy pulses are arranged inrepeated sequences and the energy pulses of each sequence have varyingcharacteristics.

Each sequence of energy pulses may include at least two pulses, as forexample, three pulses. The varying characteristic may be pulse energy,frequency, or bandwidth.

The imaging engine may include a processor that processes the reflectedultrasonic energy pulses in image frames and a detector that detects thevarying characteristic in the reflected ultrasonic energy pulses. Theimaging engine processes the frames according to the detected varyingcharacteristic.

The imaging engine may be arranged to process only reflected ultrasonicenergy pulses having a common detected characteristic. The imagingengine may be further arranged to provide a composite image based uponthe varying characteristics of the sequences of reflected ultrasonicenergy pulses.

The imaging engine may include a processor that processes the reflectedultrasonic energy pulses in separate image frames, each image framecorresponding to each different energy pulse characteristic and theimaging engine may provide display signals for simultaneously displayingthe separate image frames.

The invention further provides a method comprising providing a catheterhaving an elongated body having a distal end and an imaging corearranged to be inserted into the elongated body, the imaging core beingarranged to transmit ultrasonic energy pulses and to receive reflectedultrasonic energy pulses. The method further includes the step ofproviding the imaging core with energy pulses to cause the imaging coreto transmit the ultrasonic energy pulses, wherein the energy pulses arearranged in repeated sequences and wherein the energy pulses of eachsequence have varying characteristics.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention, together with further features and advantages thereof,may best be understood by making reference to the following descriptionstaken in conjunction with the accompanying drawings, in the severalfigures of which like reference numerals identify identical elements,and wherein:

FIG. 1 is a high-level diagram of an IVUS system;

FIG. 2a is a block diagram of signal processing paths of an IVUS systemfor co-registered imaging;

FIG. 2b is another block diagram of signal processing paths of an IVUSsystem for co-registered imaging;

FIGS. 3a and 3b illustrate a time-domain signal and power spectrum,respectively, of short-time pulses;

FIG. 4a illustrates a pass band of a broadband power spectrum;

FIG. 4b illustrates another pass band of a broadband power spectrum;

FIG. 5a is a block diagram of an imaging engine;

FIG. 5b is another block diagram of an imaging engine;

FIG. 5c is still another block diagram of an imaging engine;

FIGS. 6a-6d illustrate first, second, third, and fourth representativetransmit pulse sequences, respectively;

FIG. 7 is a block diagram of signal processing paths of an IVUS systemfor co-registered imaging;

FIG. 8 is a block diagram of signal processing steps for calculation ofan integrated backscatter parameter;

FIG. 9 illustrates a display comprising multiple co-registered images;

FIGS. 10a and 10b illustrate feature mapping between co-registeredimages;

FIG. 11 is a high-level diagram of an IVUS system;

FIG. 12 is a block diagram of a further imaging engine;

FIGS. 13-17 are block diagrams of digital signal processing engines;

FIG. 18 is a block diagram of the signal processing path of an IVUSsystem for co-registered imaging;

FIG. 19 is a cross-sectional view of a stenosed coronary artery;

FIG. 20 is a cross-sectional view of a coronary artery with an implantedstent;

FIG. 21 shows a transverse IVUS image of a stented coronary arteryacquired using a high-transmit energy pulse;

FIG. 22 illustrates a repeating high-energy, medium-energy, andlow-energy transmit pulse sequence;

FIG. 23 shows a transverse IVUS image of a stented coronary arteryacquired using a medium-transmit energy pulse;

FIG. 24 shows a transverse IVUS image of a stented coronary arteryacquired using a low-transmit energy pulse;

FIG. 25 shows a transverse IVUS image with a selected dynamic range of astented coronary artery acquired using a high-transmit energy pulse;

FIG. 26 shows a transverse IVUS image with a selected dynamic range of astented coronary artery acquired using a medium-transmit energy pulse;

FIG. 27 shows the stent regions of a transverse IVUS image with aselected dynamic range of a stented coronary artery acquired using alow-transmit energy pulse;

FIG. 28 shows a composite image of a high-transmit energy transverseIVUS image of a stented coronary artery, a medium-transmit energytransverse IVUS image of a stented coronary artery, and a low-transmitenergy transverse IVUS image of a stented coronary artery; and

FIG. 29 is a flow diagram of the signal processing path of an IVUSsystem for imaging with a high-transmit, medium-transmit andlow-transmit energy pulse sequence.

DETAILED DESCRIPTION

FIG. 1 is a high-level block diagram of an IVUS system comprised of anIVUS imaging catheter 1000, a patient interface module 2000, and animaging engine 3100. The catheter is typically delivered to a coronaryartery via a transfemoral or transradial retrograde route. The imagingcatheter 1000 is coupled mechanically and electrically to the patientinterface module 2000. The imaging engine 3100 is used to controloperation of the patient interface module 2000 and catheter 1000 forpurposes of coronary artery imaging. The following descriptions of anIVUS imaging catheter are directed to the case of a mechanicallyrotating imaging core. Each IVUS image comprises a pre-determined numberof vectors (or scan lines) and samples per vector. Most currentlyavailable commercial IVUS systems utilize 256 vectors per image. Thenumber of samples per vector varies generally between approximately 256and 2048 samples for commercially available IVUS systems and depends inpart on imaging frequency and data type (e.g., RF or baseband).

FIG. 2a is a block diagram of one embodiment of signal processing pathsof an IVUS system for co-registered imaging. A waveform is selected instep 102, generally within the imaging engine. A transmit waveform isthen generated by a transmit pulser in step 104 that is generallylocated in the patient interface module. The transmit waveform is sentthrough a transmit/receive (T/R) switch in step 106 to an ultrasoundtransducer 1100. The transducer may operate over frequency ranges of 10MHz to 80 MHz, generally between 20 MHz and 60 MHz for intracoronaryimaging.

The transducer emits an ultrasonic pressure field 1110 to insonify thecoronary artery. Some ultrasonic energy is backscattered and received bythe transducer. The received ultrasound passes through the T/R switch instep 106 and a rotary coupler in step 108. The rotary coupler may be aninductive rotary coupler or a liquid metal rotary coupler.Alternatively, the rotary coupler may be a rotary capacitive coupler asdescribed, for example, in co-pending U.S. patent application Ser. No.12/465,853 filed May 14, 2009, in the names of Silicon Valley MedicalInstruments, Inc. and titled IVUS System with Rotary CapacitiveCoupling, which application is hereby incorporated herein by referencein its entirety. The rotary coupler interfaces the mechanically rotatingimaging core of the catheter to the non-rotating electronics of thepatient interface module.

The received signal then passes through a gain amplifier in step 109, ahigh-pass filter in step 110, and a time-gain compensation amplifier instep 112. The time-gain compensation is provided, because of theincreased attenuation of the ultrasound signal as the signal propagatesfurther into the coronary artery. The signal is next sent through ananti-aliasing low-pass filter in step 114 before digitization in step116.

The digitized signals are then processed according to multi-frequencytechniques comprising a low-frequency path 120 and a high-frequency path130. The low-frequency and high-frequency processing paths comprisesimilar processing stages that may differ due to imaging parameters suchas pass band, field of view, and signal-to-noise ratio.

Referring now to FIGS. 3 and 4, the time-domain response 202 and powerspectrum 204 are respectively shown in FIGS. 3a and 3b for a short-timepulse of a 60 MHz IVUS imaging transducer having a fractionalbandwidth >60%. An important aspect of the present invention is the useof transducers with large fractional bandwidths, generally >50%fractional bandwidth. Transducers having fractional bandwidths <50% mayalso be used, but the use of such transducers is expected to be lesseffective with reduced utility. Another important aspect of the presentinvention is the use of transducers with uniformly high sensitivitiesacross the useful bandwidths. The selected low and high frequencies maycomprise overlapping bandwidths 222, 224 or non-overlapping bandwidths226, 228 with corresponding pass band center frequencies F1, F2 asillustrated respectively in FIGS. 4a and 4b . A potential benefit of theuse of overlapping bandwidths is that wider bandwidths generate imageshaving better spatial resolution. In one embodiment of the presentinvention, the low pass band center frequency F1 is 40 MHz, the highpass band center frequency F2 is 60 MHz, the low pass band 222 is 30 MHzto 50 MHz, and the high pass band 224 is 45 MHz to 75 MHz. In anotherembodiment of the present invention, the catheter comprises a broadband40 MHz transducer, the low pass band center frequency is 30 MHz, and thehigh pass band center frequency is 50 MHz. In still another embodimentof the present invention, the catheter comprises a broadband 35 MHztransducer, the low pass band center frequency is 25 MHz, and the highpass band center frequency is 40 MHz.

Referring again to FIG. 2a , the low-frequency path digitized data arefirst pre-processed in step 122. Pre-processing, as known in the art,may generally comprise bandpass filtering and vector processingtechniques. The envelope of the pre-processed data is detected in step124 followed by post-processing in step 126. Post-processing generallycomprises logarithmic compression and gamma correction to generate avisually appealing and useful image. The post-processed data are thenscan converted in step 128 from polar coordinates to Cartesiancoordinates. Pre-processing, detection, post-processing, and scanconversion are signal and image processing techniques known to thoseskilled in the art of medical ultrasound imaging.

The high-frequency path digitized data are processed in an analogousmanner. The high-frequency path digitized data are first pre-processedin step 132. Pre-processing, again, generally comprises bandpassfiltering and vector processing. The envelope of the pre-processed datais detected in step 134 followed by post-processing in step 136.Post-processing generally comprises logarithmic compression and gammacorrection to generate a visually appealing and useful image. Thepost-processed data are then scan converted in step 138 from polarcoordinates to Cartesian coordinates.

The low-frequency and high-frequency scan-converted images 152, 154 arethen simultaneously displayed in step 150. A low-frequency imagecomprises better contrast between blood and non-blood tissues tofacilitate lumen border detection. A high-frequency image comprisesbetter spatial resolution of lesion features such as thin fibrous caps.The low-frequency and high-frequency scan-converted images 152,154 areco-registered, because the same ultrasound data are used to generateboth images.

The signal processing paths illustrated in FIG. 2a can be implemented innumerous physical configurations. An important aspect of the presentinvention is the physical configuration of the imaging engine. FIG. 5ais a block diagram for one embodiment of the imaging engine 3100comprising a single board computer 3102, a dedicated digital signalprocessing (DSP) module 3120, and an interface board 3180. The DSPmodule 3120 is used to select the transmit waveform 3182 to be sent tothe patient interface module. The time-gain compensation amplifier 3184and anti-aliasing low-pass filter 3186 are located on the interfaceboard 3180. The analog-to-digital converter (or digitizer) 3128 islocated in the DSP module 3120. The DSP module 3120 may further comprisea field-programmable gate array (FPGA) 3122. The low-frequency signaland high-frequency signal processing paths 120,130 illustrated in FIG.2a are generally implemented in the FPGA. An important aspect of thisembodiment is that the co-registered imaging is performed by an imagingengine comprising a single analog-to-digital converter and a singleFPGA.

FIG. 5b is a block diagram of another embodiment of the imaging engineof the present invention comprising a first DSP module 3120 and a secondDSP module 3140 wherein a single analog-to-digital converter (ordigitizer) 3128 and two FPGAs 3122, 3142 are available. The addition ofa second DSP module comprising an FPGA provides increased computationalprocessing power at the expense of increased device complexity and cost.The same digitized data are processed by both FPGAs.

FIG. 5c is a block diagram of still another embodiment of the imagingengine of the present invention comprising a first DSP module 3120 and asecond DSP module 3140 wherein two analog-to-digital converters (ordigitizers) 3128, 3148 and two FPGAs 3122, 3142 are available. Asampling clock 3126 synchronizes both digitizers 3128, 3148. Theembodiment of the 2 digitizer/2 FPGA imaging engine further comprises asecond time-gain compensation amplifier 3188 and second anti-aliasinglow-pass filter 3190. The addition of a second digitizer 3148, time-gaincompensation amplifier 3188, low-pass filter 3190 provides increasedcomputational processing power and flexibility at the expense ofincreased device complexity. The added flexibility enables compensationfor differing attenuation of the ultrasound pressure wave through thetissue resulting from the different frequency bands.

FIG. 2b is a block diagram of another embodiment of signal processingpaths of an IVUS system for co-registered imaging comprising anembodiment of the imaging engine illustrated in FIG. 5c . The signalscattered back from the tissue is received by the transducer 1100 andthen passes through a transmit/receive switch in step 106, a rotarycoupler in step 108, a gain amplifier in step 109, and a high-passfilter in step 110. The high-pass filtered signals are then processedaccording to multi-frequency techniques comprising a low-frequencyprocessing path 120A and a high-frequency processing path 130A. Thelow-frequency processing path 120A and high-frequency processing path130A include similar processing stages that may differ due to imagingparameters such as pass band, field of view, and signal-to-noise ratio.Time-gain compensation in step 112 is first applied to the low-frequencypath signal. Time-gain compensation is provided, because of theincreased attenuation of the ultrasound signal as the signal propagatesfurther into the coronary artery. The TGC-amplified low-frequency pathsignal is next sent through an anti-aliasing low-pass filter in step 114before analog-to-digital (A/D) conversion (or digitization) in step 116.The low-frequency path digitized data are first pre-processed in step122. Pre-processing generally comprises bandpass filtering and vectorprocessing techniques. The envelope of the pre-processed data isdetected in step 124 followed by post-processing in step 126.Post-processing generally comprises logarithmic compression and gammacorrection to generate a visually appealing and useful image. Thepost-processed data are then scan converted in step 128 from polarcoordinates to Cartesian coordinates.

The high-frequency path 130A signals are processed in an analogousmanner. Time-gain compensation in step 112A, anti-aliasing low-passfilter in step 114A, and A/D conversion in step 116A occur first afterhigh-pass filtering in step 110. The high-frequency digitized data arethen pre-processed in step 132. Pre-processing generally comprisesbandpass filtering and vector processing. The envelope of thepre-processed data is detected in step 134 followed by post-processingin step 136. Post-processing generally comprises logarithmic compressionand gamma correction to generate a visually appealing and useful image.The post-processed data are then scan converted in step 138 from polarcoordinates to Cartesian coordinates. The low-frequency andhigh-frequency scan-converted images 152, 154 are then simultaneouslydisplayed in step 150. The multi-frequency signal processing paths splitafter high-pass filtering in step 110 in the embodiment of the signalprocessing paths shown in FIG. 2b whereas the multi-frequency signalprocessing paths split after A/D conversion in step 116 in theembodiment of the signal processing paths shown in FIG. 2a . The splitof the multi-frequency signal processing paths after high-pass filteringprovides for time-gain compensation appropriate for different imagingfrequencies.

Referring now to FIGS. 6a-6d , a series of imaging waveform sequencesare illustrated. FIG. 6a illustrates one embodiment in which a singlepulse sequence 10 comprises transmitting the same waveform Xc for eachvector of an IVUS image. FIG. 6b illustrates another embodimentcomprising a pulse sequence 20 of alternating low-frequency X1 andhigh-frequency X2 waveforms. A potential advantage of an alternatingpulse sequence over a single pulse sequence is that the transmittedenergy can be increased or decreased for the selected pass bands of themulti-frequency processing. The ability to adjust transmit energy maybenefit image quality of co-registered images that are simultaneouslydisplayed. FIG. 6c illustrates still another embodiment comprising apulse sequence 30 of alternating imaging Xi and parametric imaging Xpwaveforms. The imaging waveform Xi may include a Xc, X1, or X2 waveform.The parametric imaging waveform Xp is selected to optimize analysis ofat least one ultrasound tissue classification parameter includingintegrated backscatter, attenuation, strain, and motion. The use of amore narrowband waveform may provide benefit to correlation-based orDoppler-based motion analysis. FIG. 6d illustrates still yet anotherembodiment including a pulse sequence 40 of alternating imaging andparametric imaging waveforms Xi, Xp wherein multiple parametric imagingwaveforms Xp are transmitted between imaging waveforms Xi. The use ofrepeated pulses may provide additional benefits for signal-to-noiseconditions.

Thus, as may be seen from the above, and in accordance with aspects ofthe present invention, an imaging engine coupled to an imaging core maybe arranged to provide the imaging core with energy pulses to cause theimaging core to transmit ultrasonic energy pulses. The energy pulses maybe arranged in repeated sequences and the energy pulses of each sequencemay have varying characteristics. For example, each sequence of energypulses may include at least two pulses. Also, the varying characteristicmay be pulse energy.

FIG. 7 shows a block diagram of one embodiment of signal processingpaths of an IVUS system for co-registered imaging wherein theco-registered images include a grayscale image 182 and a parametricimage 184. The parametric image 184 may include a multi-parametricimage. The transmit waveform selected in step 102 and sent from theimaging engine may include a single pulse sequence 10 or an imaging andparametric imaging pulse sequence 30 as illustrated in FIGS. 6a and 6c .The signal processing path to the digitization step 116 is similar tothe signal processing path for the multi-frequency imaging illustratedin FIG. 2 a.

The digitized signals are then processed according to a grayscaleimaging path 160 and a parametric imaging path 170. The grayscaleimaging path digitized data are first pre-processed in step 162.Pre-processing generally comprises bandpass filtering and vectorprocessing techniques. The envelope of the pre-processed data isdetected in step 164 followed by post-processing in step 166.Post-processing generally comprises logarithmic compression and gammacorrection to generate a visually appealing and useful image. Thepost-processed data are then scan converted in step 168 from polarcoordinates to Cartesian coordinates.

The processing stages of the parametric imaging path 170 include apre-processing step 172, a parametric analysis step 174, apost-processing step 176, and a scan conversion step 178. The particulardetails of each parametric imaging processing step depend upon the atleast one parameter to be calculated.

In one embodiment of the present invention a parametric image ofintegrated backscatter is generated. The integrated backscatterpre-processing step 172 comprises bandpass filtering and vectorprocessing techniques. The filter pass band may be determined from the−3 dB bandwidth of the transducer. The integrated backscatter parametricanalysis in step 174 may include a sliding window technique. Slidingwindow techniques are known to those skilled in the art of ultrasoundtissue characterization.

Referring now to FIG. 8, a block diagram illustrates one embodiment ofthe signal processing stages for calculation of the integratedbackscatter parameter using a sliding window technique. A region ofinterest (ROI) of the pre-processed data 500 is first selected in step502. A time-domain window such as a Hamming or Hann window may beapplied to each vector of the ROI to minimize edge discontinuities inFast Fourier Transform (FFT) spectral analysis at the cost of reducedfrequency resolution. The ROI comprises a pre-determined number ofvectors and vector samples. The number of vectors and vector samplesdepends upon details including vector density, sample rate, optimal ROIsize, and signal-to-noise metrics.

In one embodiment of the present invention the system provides a vectordensity of 1024 vectors per IVUS image and a sample rate of400.times.10.sup.6 samples/s. An optimal ROI size balances a minimalradial extent of the ROI with a maximal signal-to-noise ratio. A lateralextent of the ROI comparable to the radial extent can facilitatesubsequent parametric image analysis. Multiple vectors also permitsignal averaging. Further, the selected ROI size may be range dependent,because the physical vector spacing increases with range. An ROI size of7 vectors and 32 samples at a range of 1.5 mm provides a ROI that isapproximately 60 .mu.m.times.60 .mu.m. This size may be suitable forsmall-scale atherosclerotic lesion features such as thin-fibrous caps.

The average power spectrum is calculated in step 504 for the ROI bycalculating the power spectrum of each vector and then averaging. Thepower spectrum is calculated generally using FFT techniques. Averagingis performed generally in the logarithmic (dB) domain, but may beperformed in the linear domain. The average power spectrum may then becompensated for system and transducer effects in step 506 comprisingrange-dependent sensitivity and frequency-dependent transducersensitivity. The integrated backscatter parameter is calculated in step508 by summing the compensated, average power spectrum values of theselected bandwidth and dividing by said selected bandwidth. AdditionalROIs are selected by sliding the window (or ROI) over the pre-processeddata 500 or pre-defined subset of the pre-processed data. The degree ofoverlap of ROIs is selected to balance smoothing in the parametric imageby maximizing overlap with computational cost by minimizing overlap. Fora ROI size of 7 vectors.times.32 samples, the sliding window overlapgenerally comprises between 16 samples (or 50%) and 24 samples (or 75%)along a vector and between 4 vectors (or approximately 50%) and 6vectors (or approximately 85%) across vectors. The integratedbackscatter parametric data are sent to the post-processing step 176 (ofFIG. 7) when there are no more ROIs remaining to be analyzed.

Post-processing in step 176 of the integrated backscatter image includesthresholding and gamma correction. In one embodiment of the presentinvention, the integrated backscatter image is thresholded to displaylipid-rich ROIs which are known to have relatively low integratedbackscatter values. In alternative embodiments, the integratedbackscatter image is thresholded at multiple levels to distinguishmultiple tissue types. The post-processed integrated backscatter imageis then scan converted in step 178.

The scan-converted grayscale image and scan-converted integratedbackscatter parametric image are then simultaneously displayed in step180. A grayscale image may provide better structural detail. Anintegrated backscatter parametric image may provide better plaquecomposition detail. Further, the grayscale and integrated backscatterparametric images 182,184 are co-registered, because the same ultrasounddata are used to generate both images.

FIG. 9 illustrates a display 190 comprising four co-registered images192, 194, 196, 198. The four co-registered images may comprise at leastone grayscale image and at least one parametric image. In one embodimentof the present invention, the display comprises a 40 MHz grayscaleimage, a 60 MHz grayscale image, and an integrated backscatterparametric image.

The present invention facilitates mapping of image features betweenco-registered images. IVUS images of lower ultrasound frequenciesgenerally provide better contrast between blood and non-blood tissueswhereas IVUS images of higher ultrasound frequencies generally providebetter spatial resolution of atherosclerotic lesions. FIG. 10aillustrates a first IVUS image 300 of lower frequency and second IVUSimage 320 of higher frequency. Catheter masks 302, 322 representcatheter position relative to a coronary artery section. A lumen contour308 identified in the first image 300 can be mapped 312 to a lumencontour 328 in the second image 320. The lumen contour segments blood304 from non-blood tissues. A vessel contour 310 identified in the firstimage 300 can be mapped 314 to a vessel contour 330 in the second image320. The lumen and vessel contours 308, 310 segment atheroscleroticplaque 306 from other tissues. The mapped contours 328, 330 of thehigher-frequency IVUS image enable further processing of theatherosclerotic plaque.

FIG. 10b illustrates mapping features more prominent in a first image340 to a second image 360 and mapping features more prominent in saidsecond image 360 to said first image 340. The first image may comprise agrayscale image, and the second image may comprise a parametric image. Alumen contour 348 in the first image 340 is mapped 352 to a lumencontour 368 in the second image 360. A vessel contour 370 and ROI 372 inthe second image 360 are respectively mapped 374, 376 to a second vesselcontour 350 and second ROI 352 in the first image 340.

It is desirable that the present invention provide optimal imagingperformance and computational efficiency with minimal device complexity.FIG. 11 shows a high-level diagram of one embodiment of an IVUS systemfor co-registered imaging. The following descriptions of an IVUS systemfor co-registered imaging are directed to the case of an IVUS system fordisplay of two co-registered grayscale images. The IVUS system comprisestwo images 3802, 3803, an imaging engine 3804, a patient interfacemodule (PIM) 2000, and an IVUS imaging catheter 1000. The followingdescriptions of the IVUS imaging catheter 1000 are directed at the caseof a mechanically rotating imaging core. The imaging engine 3804comprises a display engine 3806, a DSP engine 3808, transmit (Tx) logic3810, a transmit buffer 3812, a receive (Rx) signal conditioning stage3814, and an analog-to-digital converter (ADC) 3816.

The DSP engine 3808 provides computing power for real-time, simultaneousco-registered imaging. The DSP engine 3808 sends control signals to thetransmit logic 3810 that generates an analog transmit pulse sequence.The transmit pulse passes through the transmit buffer 3812 before goingto the PIM 2000. The PIM 2000 is the interface between the catheter 1000and the imaging engine 3804. The PIM 2000 provides for transmittingtransducer excitation energy, receiving transducer signal returns, andsending signal returns to the imaging engine 3804. The return signalspass through a receive signal conditioning stage 3814 andanalog-to-digital converter 3816. The digitized return signals are thenprocessed in the DSP engine 3808. Image data are sent to the displayengine 3806 and streamed for real-time simultaneous display ofco-registered images 3802, 3803.

FIG. 12 illustrates one embodiment of a physical configuration of theimaging engine 3100. The imaging engine 3100 performs all imagegeneration, display, and control of the entire system. The imagingengine 3100 may include a general processing unit 3500, a DSP module3600, and an interface board 3700.

The general processing unit 3500 may include a central processing unit(CPU) 3502, a memory controller 3504, dynamic random access memory(DRAM) 3506, a digital bus interface 3508, and a peripheral controller3510. The DSP module 3600 may include a DSP engine 3610, transmit logiccircuitry 3612, a digital-to-analog converter (DAC) 3620, ananalog-to-digital converter (ADC) 3630, and a sampling clock 3640. Ahigh-speed digital bus 3512 connects the digital bus interface 3508 tothe DSP engine 3610. The interface board 3700 may include a transmitbuffer 3702, a time gain compensation (TGC) amplifier 3704, and ananti-aliasing low-pass filter (LPF) 3706.

The DSP engine 3610 controls the transmit logic circuitry 3612 to sendan analog transmit signal to the transmit buffer 3702. The analogtransmit signal may include a pulse wherein the pulse may include atleast one rectangular pulse. The analog transmit signal is sent from theinterface board 3700 to the PIM. The DSP engine 3610 further generates adigital TGC signal that is converted by the DAC 3620 to an analog TGCsignal. The analog TGC signal provides the level of TGC amplification3704 applied to signals received from the PIM. The low-pass filter 3706minimizes aliasing in the TGC-amplified signals.

The anti-aliased TGC-amplified return signals are digitized and thenprocessed by the DSP engine 3610 for co-registered imaging. A samplingclock 3640 synchronizes the ADC (or digitizer) 3630 and DSP engine 3610.Co-registered images are streamed from the DSP engine 3610 to thegeneral processing unit 3500 for display of images.

Referring now to FIGS. 13-17, the DSP engine 3610 may include differentforms of signal processors. FIGS. 13-15 show diagrams of a DSP engine3610 including a field-programmable gate array (FPGA) 3902, a DSP chip3904 and random-access memory (RAM) 3906, or an application-specificintegrated circuit (ASIC) 3908. The DSP engine may further includemultiple signal processors. FIG. 16 shows a diagram of a DSP engine 3610that includes a first FPGA 3910 and a second FPGA 3912. FIG. 17 shows adiagram of a DSP engine 3610 that includes a massively parallelprocessor array (MPPA) 3914 of CPUs and RAM modules. The most costeffective and computationally efficient signal processor will depend onthe specific application. Field-programmable gate arrays are commonlyused in IVUS imaging systems.

FIG. 18 illustrates a signal processing path for co-registeredmulti-frequency imaging that provides for optimizing co-registeredgrayscale imaging performance while minimizing device cost andcomplexity. The following descriptions are directed at the case of analternating transmit pulse sequence 20 as illustrated in FIG. 6b whereina first pulse sequence X1 has a lower imaging frequency and a secondpulse sequence X2 has a higher imaging frequency. A potential advantageof the alternating pulse sequence 20 over a single pulse sequence 10shown in FIG. 6a is that the transmitted energy can be increased ordecreased for the selected pass bands of the multi-frequency processing.The ability to adjust transmit energy may benefit image quality ofco-registered images that are simultaneously displayed.

The received signal is converted from analog to digital (A/D) in step300. The digitized signals are pre-processed in step 302 whereinpre-processing generally includes bandpass filtering and vectorprocessing techniques. The specific form of pre-processing depends onwhether the transmit signal is an X1 pulse or X2 pulse. A digitalmultiplexer 330 receives a first set of pre-processing coefficients 332and a second set of pre-processing coefficients 334. The pre-processingcoefficients include filter coefficients for band-pass filtering. Avector processing control 320 determines which set of pre-processingcoefficients to use for pre-processing. The envelope of thepre-processed signal is detected in step 304. The vector processingcontrol 320 determines whether a digital multiplexer 340 selects a firstset of detection coefficients 342 or a second set of detectioncoefficients 344 for detection processing. The detected signal is thenpost-processed in step 306 wherein post-processing generally compriseslogarithmic compression and gamma correction to generate a visuallyappealing and useful image. The post-processed signals are then scanconverted in step 308 from polar coordinates to Cartesian coordinates.

The low-frequency and high-frequency scan-converted images 312, 314 arethen simultaneously displayed in step 310. A low-frequency image mayprovide better contrast between blood and non-blood tissues tofacilitate lumen border detection. A high-frequency image may providebetter spatial resolution of lesion features. The low-frequency andhigh-frequency scan-converted images 312,314 are co-registered, becauseboth sets of image data are acquired at substantially the same time whenusing alternating transmit pulse sequences.

In another embodiment, the alternating transmit pulse sequence mayinclude alternating groups of pulses. A pulse sequence may includealternating groups of X1 and X2 pulse sequences wherein each group of X1and X2 pulses includes at least two (2) pulses. The temporal delay willbe larger between acquisitions of the X1 and X2 images, but there may beadvantages to fewer alternations between X1 and X2 pulse sequences.

A key advantage of the signal processing path illustrated in FIG. 18 isthat only one digitizer is required. Further, the digital signalprocessing can be performed in a single FPGA. Still further, themulti-frequency processing can be performed without duplication ofsignal processing stages.

An important aspect of the present invention is the use of an IVUSsystem for co-registered imaging comprising an imaging engine, a patientinterface module, and an IVUS catheter. The imaging engine may comprisea general processing unit, a DSP module, and an interface board. The DSPmodule comprises an analog-to-digital converter and a DSP engine. TheDSP engine may comprise a FPGA, DSP chip, or ASIC. The DSP engine mayalternatively comprise multiple FPGAs or a massively parallel processingarray of CPUs and RAM modules. Another important aspect of the presentinvention is the use of an IVUS catheter comprising a broadband (>50%fractional bandwidth) ultrasound transducer with high sensitivitywherein both a low pass band and a high pass band can be used togenerate grayscale images. Low pass band and high pass band centerfrequencies may respectively comprise 40 MHz and 60 MHz, 30 MHz and 50MHz, 25 MHz and 40 MHz, and other combinations with different frequencyspacing. Still another important aspect of the present invention is theuse of a programmable transmit pulse sequence. The transmit pulsesequence may comprise a single pulse imaging sequence, an alternatinglow-frequency and high-frequency imaging sequence, or an alternatingimaging and parametric imaging sequence. Still yet another importantaspect of the present invention is the display of at least two (2)co-registered images comprising at least one grayscale image. Theco-registered images may further comprise at least one parametric image.A further important aspect of the present invention is the mapping ofimage features between co-registered images wherein image featurescomprise contours and regions of interest.

It is also desirable to provide improved contrast resolution for imagingof coronary arteries having implanted stents. The ability to detect andmeasure stent healing, or early neotissue growth over coronary stentstruts, is of particular relevance. FIG. 19 shows an illustration of across-section of a stenosed coronary artery 400. The coronary arteryincludes a blood-filled lumen 402, an intimal plaque layer 404, a mediallayer 406, and an adventitial layer 408. The lumen generally has across-sectional area less than 4 mm.sup.2. FIG. 20 shows an illustrationof the same coronary artery 400 as in FIG. 19 after stent implantation.The stent struts 410 are positioned in proximity to the lumen-plaqueborder. The stent provides for an increased lumen cross-sectional areato enable improved blood flow through the artery.

FIG. 21 shows a transverse IVUS image 420 of a stented coronary arteryacquired with a high-transmit energy pulse having an amplitude generallygreater than 50 V. The transverse IVUS image 420 includes a cathetermask 422 to indicate position of the IVUS catheter relative to thecoronary artery. The IVUS image 420 further shows ultrasound reflectionsfrom a blood-filled lumen 424, neotissue growth 426, an intimal plaquelayer 428, a medial layer 430, and an adventitial layer 432. Theneotissue growth 426 is a result of the stent healing process. Uncoveredstruts of drug-eluting stents are considered a factor in the adverseevent of late stent thrombosis. The transverse IVUS image 420 stillfurther includes substantially strong ultrasound reflections from thestent struts 434 as well as so-called stent blooming artifacts 436. Thestent blooming artifacts can result from saturation of the receive-sideelectronics that are part of the IVUS system and characteristicallyappear on the side of the stent struts 434 away from the catheter mask422. The combined thickness of the stent reflection 434 and stentblooming artifact 436 is generally substantially larger than thephysical thickness of the stent struts, which is approximately 100microns or smaller. The stent blooming artifacts 436 degrade imagequality.

Stent blooming artifacts can be prevented by sufficiently decreasing theenergy of the transmit pulse to avoid saturation of the receive-sideelectronics of the IVUS system. In one embodiment of the presentinvention, a three-pulse sequence that includes a high-transmit energypulse, a medium-transmit energy pulse, and a low-transmit energy pulsemay be used to visualize neotissue growth, provide adequate penetrationof the ultrasound energy into the coronary artery, and prevent stentblooming artifacts. FIG. 22 illustrates a repeating pulse sequence 22 ofhigh-energy transmit pulses XH, medium-energy transmit pulses XM, andlow-energy transmit pulses XL.

The transverse IVUS image 420 shown in FIG. 21 is acquired with ahigh-transmit energy pulse and enables visualization of neotissue growthand penetration beyond the medial layer 430. FIG. 23 shows a transverseIVUS image 440 of the same stented coronary artery shown in FIG. 21, butacquired with a medium-transmit energy pulse having an amplitude lessthan the amplitude of the high-transmit energy pulse. The transverseIVUS image 440 includes a catheter mask 422 to indicate position of theIVUS catheter relative to the coronary artery. The IVUS image 440further shows ultrasound reflections from a blood-filled lumen 424,neotissue growth 426, and an intimal plaque layer 428. The transverseIVUS image 440 still further includes ultrasound reflections from thestent struts 442 and stent blooming artifacts 444.

FIG. 24 shows a transverse IVUS image 450 of the same stented coronaryartery shown in FIG. 21, but acquired with a low-transmit energy pulsehaving an amplitude less than the amplitude of the high-transmit energypulse. The transverse IVUS image 450 includes a catheter mask 422 toindicate position of the IVUS catheter relative to the coronary artery.The IVUS image 440 further shows ultrasound reflections from neotissuegrowth 426 and parts of the intimal plaque layer 428. The transverseIVUS image 440 still further includes ultrasound reflections from thestent struts 454. Because of the low-transmit energy level of the pulse,there will be no stent blooming artifact and more distant sections ofthe coronary artery such as the medial and adventitial layers may not bevisualized. The low-transmit energy level of the pulse may degrade theability to detect and visualize the small ultrasound reflections from ablood-filled lumen.

A high-transmit energy IVUS image, a medium-transmit energy IVUS image,and a low-transmit energy IVUS image can be co-registered by using asequence of repeated high-transmit energy, medium-transmit energy andlow-transmit energy pulses. Referring now to FIG. 25, a high-transmitenergy IVUS image 460 can be further processed to include deeper tissuesthat are visualized with a high-transmit energy pulse such as the mediallayer 430 and the adventitia 432. Referring now to FIG. 26, amedium-transmit energy IVUS image 470 can be further processed to havesections 472 of the image that include the stents and stent bloomingartifacts removed from the image. Referring now to FIG. 27, alow-transmit energy IVUS image 480 can be further processed to includethe neotissue growth 426 and only those sections 454,472 that map to thesections of the medium-transmit energy IVUS image 470 that include thestents and stent blooming artifacts 472. Referring now to FIG. 28, thefurther processed high-transmit energy IVUS image 460 the furtherprocessed medium-transmit energy IVUS image 470, and the furtherprocessed low-transmit energy IVUS image 480 can be combined into acomposite image 490 that visualizes neotissue growth 426 over stentstruts 454, visualizes tissue beyond and including the medial layer 430,and avoids stent blooming artifacts.

FIG. 29 illustrates one embodiment of a signal processing pathgenerating a composite image from images acquired using high-transmit,medium-transmit, and low-transmit energy pulses. The followingdescriptions are directed to the case of an transmit pulse sequence 22as illustrated in FIG. 22 wherein a first pulse XH has a high-transmitenergy, a second pulse XM has a medium-transmit energy, and a thirdpulse XL has a low-transmit energy.

A high-transmit energy, medium-transmit energy, or low-transmit energywaveform, generally stored within an imaging engine, is selected in step550. A transmit waveform is then generated by a transmit pulser in step552. The transmit waveform is sent through a transmit/receive (T/R)switch in step 554 to an ultrasound transducer 1100. The transducer mayoperate over frequency ranges of 10 MHz to 80 MHz, generally between 20MHz and 60 MHz for intracoronary imaging.

The transducer emits an ultrasonic pressure field 1110 to insonify thecoronary artery. Some ultrasonic energy is backscattered and received bythe transducer. The received ultrasound passes through the T/R switch instep 554 and a rotary coupler in step 556. The rotary coupler may be aninductive rotary coupler or a liquid metal rotary coupler. The rotarycoupler interfaces the mechanically rotating imaging core of thecatheter to the non-rotating electronics of the patient interfacemodule.

Gain is then applied to the received signal in step 558. A high-passfilter is next applied to the amplified signal in step 560. Atime-varying gain is applied to the high-pass filtered signal in step562. The time-gain compensation is provided, because of the increasedattenuation of the ultrasound signal as the signal propagates furtherinto the coronary artery. An anti-aliasing low-pass filter is nextapplied to the signal in step 564 before the signal is digitized in step566.

The digitized signals are pre-processed in step 568 whereinpre-processing generally includes band-pass filtering and vectorprocessing techniques. The specific form of pre-processing depends onwhether the transmit signal is a high-transmit energy pulse XH or alow-transmit energy pulse XL. A digital multiplexer 584 receives a firstset of pre-processing coefficients PH 584, a second set ofpre-processing coefficients PM 585, and a third set of pre-processingcoefficients PL 586. The pre-processing coefficients include filtercoefficients for band-pass filtering. A vector processing control 580determines which set of pre-processing coefficients to use forpre-processing. The envelope of the pre-processed signal is detected instep 570. The vector processing control 580 determines whether a digitalmultiplexer 588 selects a first set of detection coefficients DH 590, asecond set of detection coefficients DM 585, or a third set of detectioncoefficients DL 592 for detection processing. The detected signal isthen post-processed in step 572 wherein post-processing generallyincludes logarithmic compression and gamma correction to generate avisually appealing and useful image.

The post-processed signals can then be scan converted from polarcoordinates to Cartesian coordinates in step 574. The high-transmitenergy, medium-transmit energy, and low-energy transmit scan-convertedimages are then combined into a composite image in step 576. Thecombination or fusion of the three images into a single composite imageare achieved by selecting a portion of the dynamic range of eachindividual image. The composite image may then have a wider dynamicrange than any single image. The composite image may then be compressedto satisfy parameters of the display device. The composite imageincludes neotissue growth over stent struts and tissue beyond andincluding the medial layer. The composite image further avoids stentblooming artifacts. The individual high-transmit energy, medium-transmitenergy, and low-transmit energy images can be first aligned duringpost-processing to minimize motion artifacts. In addition, the imagescan be acquired during a period of relatively little motion, such as enddiastole of the cardiac cycle, to further minimize motion artifacts.Motion artifacts can be further minimized by minimizing the depth orrange of acquired data in order to minimize time between pulsetransmissions.

While particular embodiments of the present invention have been shownand described, modifications may be made, and it is therefore intendedto cover in the appended claims all such changes and modifications whichfall within the true spirit and scope of the invention.

1-12. (canceled)
 13. An intravascular ultrasound imaging systemcomprising: a catheter including an imaging core configured to transmitultrasonic energy pulses in a repeating sequence that contains a firstpredefined ultrasonic energy pulse characteristic and a secondpredefined ultrasonic energy pulse characteristic, the imaging corefurther configured to receive reflected ultrasonic energy pulses; and animaging engine coupled to the imaging core to receive the reflectedultrasonic energy pulses, the reflected ultrasonic energy pulsesincluding first image data acquired from the first predefined ultrasonicenergy pulse characteristic and second image data acquired from thesecond predefined ultrasonic energy pulse characteristic, the imagingengine configured to: select a portion of the first image datarepresenting a processed first image that is based on the selectedportion of the first image data, select a portion of second image datarepresenting a processed second image that is based on the selectedportion of the second image data, and combine the selected portion ofthe first image data and the selected portion of the second image datato create a composite image.
 14. The system of claim 13, wherein theimaging engine is further configured to co-register the first image dataacquired from the first predefined ultrasonic energy pulsecharacteristic and the second image data acquired from the secondpredefined ultrasonic energy pulse characteristic.
 15. The system ofclaim 13, wherein the first predefined ultrasonic energy pulsecharacteristic comprises a first transmit energy pulse and the secondpredefined ultrasonic energy pulse characteristic comprises a secondtransmit energy pulse that is less than the first transmit energy pulse.16. The system of claim 15, wherein the selected portion of the firstimage data comprises image data representing a first structure acquiredat the first transmit energy pulse at a first distance from the imagingcore, and wherein the selected portion of the second image datacomprises image data representing a second structure acquired at thesecond transmit energy pulse at a second distance from the imaging corethat is less than the first distance.
 17. The system of claim 16,wherein the second distance is adapted to be a distance that a stent islocated from the imaging core.
 18. The system of claim 17, wherein thesecond transmit energy pulse is adapted to prevent a stent bloomingartifact.
 19. The system of claim 17, wherein the first distance isadapted to be a distance that a medial tissue layer is located from theimaging core.
 20. The system of claim 19, wherein the first distance isfurther adapted to be a distance that an adventitial tissue layer islocated from the imaging core.
 21. The system of claim 16, wherein imagedata representing the second structure comprises image data representinga stent, and wherein image data representing the first structurecomprises image data representing a medial tissue layer and anadventitial tissue layer.
 22. The system of claim 13, wherein thecomposite image includes the selected portion of the first image datarepresenting a medial tissue layer and the selected portion of thesecond image data representing neotissue growth over a stent, andwherein the composite image has characteristics such that no stentblooming artifact is included in the composite image.
 23. The system ofclaim 22, further comprising a display configured to visually presentthe composite image.
 24. The system of claim 13, wherein the firstpredefined ultrasonic energy pulse characteristic and the secondpredefined ultrasonic energy pulse characteristic are received at theimaging core at substantially the same time.
 25. The system of claim 13,wherein the imaging core is further configured to transmit ultrasonicenergy pulses in the repeating sequence that contains a third predefinedultrasonic energy pulse characteristic, wherein the reflected ultrasonicenergy pulses include third image data acquired from the thirdpredefined ultrasonic energy pulse characteristic, and wherein theimaging engine is further configured to select a portion of the thirdimage data representing a processed third image that is based on theselected portion of the third image data and combine the selectedportion of the first image data, the selected portion of the secondimage data, and the selected portion of the third image data to createthe composite image.
 26. The system of claim 25, wherein the thirdpredefined ultrasonic energy pulse characteristic comprises a thirdtransmit energy pulse that is less than the first transmit energy pulseand greater than the second transmit energy pulse.
 27. A methodcomprising: co-registering first image data acquired from a reflectedfirst predefined ultrasonic energy pulse characteristic and second imagedata acquired from a reflected second predefined ultrasonic energy pulsecharacteristic; selecting a portion of the first image data representinga processed first image that is based on the selected portion of thefirst image data; selecting a portion of the second image datarepresenting a processed second image that is based on the selectedportion of the second image data; and combining the selected portion ofthe first image data and the selected portion of the second image datato create a composite image.
 28. The method of claim 27, wherein thefirst image data is acquired from the reflected first predefinedultrasonic energy pulse characteristic at substantially a same time asthe second image data is acquired from the reflected second predefinedultrasonic energy pulse characteristic.
 29. The method of claim 27,wherein the reflected first predefined ultrasonic energy pulsecharacteristic corresponds to a first transmit energy pulse and thereflected second predefined ultrasonic energy pulse characteristiccorresponds to a second transmit energy pulse that is less than thefirst transmit energy pulse.
 30. The method of claim 29, wherein theselected portion of the first image data comprises image datarepresenting a first structure acquired at the first transmit energypulse at a first distance from an imaging core, and wherein the selectedportion of the second image data comprises image data representing asecond structure acquired at the second transmit energy pulse at asecond distance from the imaging core that is less than the firstdistance.
 31. The method of claim 30, wherein the second distance is adistance that a stent is located from the imaging core, and wherein thefirst distance is a distance that a medial tissue layer is located fromthe imaging core.
 32. The method of claim 27, wherein the compositeimage includes the selected portion of the first image data representinga medial tissue layer and the selected portion of the second image datarepresenting neotissue growth over a stent, and wherein the compositeimage has characteristics such that no stent blooming artifact isincluded in the composite image.